Patent Application
20120093881
The present invention relates to a polymer micelle composition and a pharmaceutical composition using the polymer micelle composition.
There are known a use of block copolymers each having a hydrophilic polymer chain segment and a hydrophobic polymer chain segment as a carrier for drugs and a method encapsulating a predetermined drug into a polymer micelle formed of the copolymers (for example, Patent Document 1 or 2). There are also known a composition including a homogeneous polymer micelle encapsulating a poorly water-soluble drug and a preparation method therefor (Patent Document 3).
Patent Document 1 or 2 describes a method encapsulating a drug into a micelle preliminarily formed from block copolymers in an aqueous medium by adding the drug to the micelle solution, and optionally, mixing and stirring the resultant under heating and ultrasonication. Further, Patent Document 3 describes a method for preparing a polymer micelle encapsulating a drug by dissolving block copolymers and drugs in a water-miscible polar solvent and then subjecting the resultant to dialysis against water.
According to those prior arts, it is understood that the use of the polymer micelle as the carrier for drugs has various advantages including a sustained release of drug. However, in a conventional polymer micelle, a drug is encapsulated into the micelle in a very stable manner, which may inhibit the drug from being released suitably.
A main object of the present invention is to provide a polymer micelle composition capable of stably encapsulating and suitably releasing a drug, and a pharmaceutical composition using the polymer micelle composition.
The present invention provides a polymer micelle composition. The polymer micelle composition comprises block copolymers each having a hydrophobic polymer chain segment and a hydrophilic polymer chain segment. A plurality of the block copolymers is arranged radially in a state in which the hydrophobic polymer chain segment is directed inward and the hydrophilic polymer chain segment is directed outward. The polymer micelle composition comprises as the block copolymers, a block copolymer having affinity with HDL and a block copolymer having affinity with a lipoprotein excluding HDL. The block copolymer having affinity with HDL has a hydrophobic polymer chain segment formed of a polyamino acid including repeating units derived from a hydrophobic derivative of an amino acid. The hydrophobic derivative of an amino acid includes a derivative obtained by introducing an aromatic group and/or a sterol residue into a side chain of the amino acid. The block copolymer having affinity with a lipoprotein excluding HDL has a hydrophobic polymer chain segment formed of a polyamino acid including repeating units derived from a hydrophobic derivative of an amino acid. The hydrophobic derivative of an amino acid includes a derivative obtained by introducing a hydrophobic group having a linear or branched structure into a side chain of the amino acid. A detachment of the block copolymer having affinity with HDL is induced by HDL adhesion attributed to the affinity. A gap in polymer micelle produced through the detachment causes promotion of release of a drug to be encapsulated, i.e., one kind selected from the group consisting of water-soluble physiologically active polypeptides and proteins each having a molecular weight of 1,500 or more. The block copolymer having affinity with a lipoprotein excluding HDL makes the gap smaller to suppress promotion of release of the drug to be encapsulated, which allows control of a release speed of the drug.
The present invention provides another polymer micelle composition in other aspect. The polymer micelle composition comprises block copolymers each having a hydrophobic polymer chain segment and a hydrophilic polymer chain segment. A plurality of the block copolymers is arranged radially in a state in which the hydrophobic polymer chain segment is directed inward and the hydrophilic polymer chain segment is directed outward. The polymer micelle composition comprises a block copolymer having affinity with HDL as one of the block copolymers. The block copolymer having affinity with HDL has a hydrophobic polymer chain segment formed of a polyamino acid including repeating units derived from a hydrophobic derivative of an amino acid. The hydrophobic derivative of an amino acid includes a derivative obtained by introducing a sterol residue into a side chain of the amino acid. The block copolymer having affinity with HDL has a hydrophilic polymer chain segment of poly(ethylene glycol). A detachment of the block copolymer having affinity with HDL is induced by HDL adhesion attributed to the affinity. A gap in the polymer micelle formed through the detachment causes promotion of release of a drug to be encapsulated, i.e., one kind selected from the group consisting of water-soluble physiologically active polypeptides and proteins each having a molecular weight of 1,500 or more.
The present invention provides a pharmaceutical composition in yet another aspect. The pharmaceutical composition comprises above mentioned polymer micelle composition and a drug encapsulated in the polymer micelle composition, i.e., one kind selected from the group consisting of water-soluble physiologically active polypeptides and proteins each having a molecular weight of 1,500 or more.
According to the present invention, there can be provided the polymer micelle composition capable of stably encapsulating and suitably releasing a drug, and the pharmaceutical composition using the polymer micelle composition.
A. Polymer Micelle Composition
A polymer micelle composition of the present invention includes block copolymers each having a hydrophobic polymer chain segment and a hydrophilic polymer chain segment. A plurality of the block copolymers are arranged radially in a state in which the hydrophobic polymer chain segment is directed inward and the hydrophilic polymer chain segment is directed outward. The polymer micelle composition includes a block copolymer having affinity with high-density lipoprotein (HDL) (hereinafter, sometimes referred to as “block copolymer with HDL affinity”) as one of the block copolymers. According to the polymer micelle composition, the detachment of the block copolymer with HDL affinity is induced by HDL adhesion attributed to the affinity, and a gap formed through the detachment causes the promotion of the release of a drug to be encapsulated. The adhesion property of the polymeric micelle to HDL may be confirmed by observing the presence of block copolymers in an HDL fraction in the case of incubating the polymer micelle composition in the presence of HDL (for example, in plasma) and then purifying the HDL fraction. The “hydrophobic polymer chain segment” and the “hydrophilic polymer chain segment” may have any suitable hydrophobic degree and hydrophilic degree, respectively, as long as a micelle in which a plurality of block copolymers each having those two segments are arranged in the above-mentioned state can be formed in an aqueous medium.
A possible reason why the release of a drug from the polymer micelle composition is promoted is as described below. As illustrated in
As the drug to be encapsulated in the polymer micelle composition, one kind selected from the group consisting of water-soluble physiologically active polypeptides and proteins each having a molecular weight of 1,500 or more is preferable. The drug has a relatively large size and hence hardly leaks from small gaps between block copolymers in a conventional type polymer micelle. Thus, the drug is not sufficiently released and is eliminated from the blood circulation together with the micelle in some cases. On the other hand, the polymer micelle composition according to the present invention exerts sustained-release performance of a drug through micelle formation, while it is also excellent for use in promoting the release of such drug having a relatively large size as compared to the conventional type polymer micelle. Further, as described later, in the polymer micelle composition according to the present invention, a block copolymer having affinity with a lipoprotein excluding HDL such as LDL or VLDL (hereinafter, sometimes referred to as “block copolymer without HDL affinity”) may also be further incorporated to control the degree of the release of a drug.
The hydrophobic polymer chain segment in the block copolymer with HDL affinity may be formed of a polyamino acid. The polyamino acid includes repeating units derived from a hydrophobic derivative of an amino acid obtained by introducing a hydrophobic group having a cyclic structure into a side chain of the amino acid. The hydrophobic derivative of an amino acid having a cyclic structure is preferably a hydrophobic derivative of an acidic amino acid such as aspartic acid and glutamic acid, and a hydrophobic group having a cyclic structure may be introduced into a carboxyl group in a side chain of the acidic amino acid.
The hydrophobic group having a cyclic structure may be a group having a monocyclic structure or a group having a polycyclic structure, and for example, may be an aromatic group, an alicyclic group, or a sterol residue. The hydrophobic group is preferably a C4 to C16 alkyl group having a cyclic structure, a C6 to C20 aryl group, a C7 to C20 aralkyl group, and a sterol residue. A sterol means a natural, semisynthetic, or synthetic compound based on a cyclopentanone hydrophenanthrene ring (C17H28) and derivatives thereof. For example, a natural sterol is exemplified by cholesterol, cholestanol, dihydrocholesterol, cholic acid, campesterol, and sitosterol. The semisynthetic or synthetic compounds may be, for example, synthetic precursors of the natural sterol (as necessary, encompassing a compound in which part or all of, if present, certain functional groups, hydroxy groups have been protected with a hydroxy protective group known in the art, or a compound in which a carboxyl group has been protected with carboxyl protective group). The sterol derivative may have a C6 to C12 alkyl group or a halogen atom such as chlorine, bromine, and fluorine introduced into a cyclopentanone hydrophenanthrene ring as long as the object of the present invention is not adversely affected. The cyclopentanone hydrophenanthrene ring may be saturated or partially unsaturated.
The hydrophobic polymer chain segment in the block copolymer with HDL affinity may have not only repeating units derived from a hydrophobic derivative of an amino acid having a cyclic structure but also other repeating units as long as the effects of the present invention are exerted. Examples of the other repeating units include: repeating units derived from an acidic amino acid such as glutamic acid and aspartic acid, and for example, a hydrophobic derivative obtained by introducing a 04 to C16 unsubstituted or substituted linear or branched alkyl group into the acidic amino acid.
The content of the repeating units derived from the hydrophobic derivative of an amino acid having a cyclic structure is preferably 10 to 100 mol %, more preferably 20 to 80 mol % with respect to the total (100 mol %) of the repeating units for forming the hydrophobic polymer chain segment in the block copolymer with HDL affinity. The above-mentioned content can provide the affinity with HDL more surely.
Examples of the hydrophilic polymer chain segment in the block copolymer with HDL affinity include poly (ethylene glycol), polysaccharide, poly(vinyl pyrrolidone), poly(vinyl alcohol), poly(acrylic amide), poly(acrylic acid), poly(methacrylic amide), poly(methacrylic acid), poly(methacrylic acid ester), poly(acrylic acid ester), polyamino acid, poly(malic acid), and derivatives thereof. Specific examples of the polysaccharide include starch, dextran, fructan, and galactan.
In the block copolymer with HDL affinity, the hydrophilic polymer chain segment and the hydrophobic polymer chain segment are linked to each other through a known linking group. Examples of the linking group include an ester bond, an amide bond, an imino group, a carbon-carbon bond, and an ether bond. The end opposite to the end at the side of the hydrophilic polymer chain segment in the hydrophobic polymer chain segment and the end opposite to the end at the side of the hydrophobic polymer chain segment in the hydrophilic polymer chain segment maybe subjected to any suitable chemical modification as long as the formation of a polymer micelle is not adversely affected.
The block copolymer with HDL affinity may have a hydrophilic polymer chain segment of poly(ethylene glycol) and a hydrophobic polymer chain segment formed of a polyamino acid including repeating units derived from a hydrophobic derivative of an amino acid. The hydrophobic derivative of an amino acid may be a derivative obtained by introducing a sterol residue into a side chain of the amino acid.
The block copolymer with HDL affinity maybe represented by each of the following general formulae (I) and (II). The polymer micelle composition of the present invention may include two or more kinds of block copolymers with HDL affinity.
In each of the above-mentioned formulae, R1 and R3 each independently represent a hydrogen atom or a lower alkyl group substituted or unsubstituted by an optionally protected functional group;
The C6 to C20 aryl group and the C7 to C20 aralkyl group are exemplified by preferably a phenyl group, a naphthyl group, a tolyl group, a xylyl group, a benzyl group, and a phenethyl group, more preferably a benzyl group. Further, a sterol from which the steryl group is derived is exemplified by preferably cholesterol, cholestanol, and dihydroxycholesterol, more preferably cholesterol.
n in each of the above-mentioned formulae represents an integer in the range of preferably 10 to 1,000, more preferably 20 to 600, particularly preferably 50 to 500. x and m in each of the above-mentioned formulae each represent an integer in the range of preferably 20 to 200, more preferably 30 to 100.
Examples of the optionally protected functional group include a hydroxyl group, an acetal, a ketal, an aldehyde, a sugar residue, a maleimide group, a carboxyl group, an amino group, a thiol group, and an active ester. The hydrophilic polymer chain segment in the case where R1 and R3 each represent a lower alkyl group substituted by an optionally protected functional group may be prepared, for example, in accordance with the methods described in WO 96/33233 A1, WO 96/32434 A1, and WO 97/06202 A1. The lower alkyl group means a linear or branched alkyl group having, for example, 7 or less, preferably 4 or less carbon atoms.
The block copolymer with HDL affinity may be obtained, for example, by coupling a polymer having a hydrophilic polymer chain and a polymer having a polyamino acid chain by a known method, each of which has not been subjected to any treatment or has been purified so as to achieve narrow molecular weight distribution as necessary. The block copolymer of the general formula (I) may also be formed, for example, by carrying out anionic living polymerization using an initiator capable of giving R1 to form a polyethylene glycol chain, then introducing an amino group at the side of the growing end, and polymerizing an N-carboxylic anhydride (NCA) of a protected amino acid such as β-benzyl-L-aspartate or γ-benzyl-L-glutamate from the amino end.
A specific example of a method of manufacturing the block copolymer with HDL affinity is described below. (i) N-carboxy-β-benzyl-L-aspartic anhydride (BLA-NCA) or (ii) N-carboxy-β-benzyl-L-glutamic anhydride (BLG-NCA) are added and subjected to a reaction using, as an initiator, polyethylene glycol, which is protected at one end and has an amino group at the other end, such as MeO—PEG-CH2CH2CH2—NH2, in a dehydrate organic solvent so as to achieve a desired polymerization degree (number of amino acid units), to thereby afford (i) polyethylene glycol-co-polyaspartic acid benzyl ester or (ii) polyethylene glycol-co-polyglutamic acid benzyl ester. In addition, the resultant block copolymer is acetylated at the end with acetyl chloride or acetic anhydride, then subjected to alkali hydrolysis to remove a benzyl group, and converted into polyethylene glycol-co-polyaspartic acid or polyethylene glycol-co-polyglutamic acid. After that, benzyl alcohol is added in an organic solvent so as to achieve a desired esterification ratio, and a reaction is carried out in the presence of a condensation agent such as N-N′-dicyclohexyl carbodiimide (DCC) and N-N′-diisopropyl carbodiimide (DIPCI) to afford a block copolymer partially having a benzyl ester.
When a reaction is performed using cholesterol in place of benzyl alcohol, polyethylene glycol-co-polyaspartic acid cholesterol ester and polyethylene glycol-co-polyglutamic acid cholesterol ester may be prepared.
Another specific example of the method of manufacturing the block copolymer with HDL affinity is a method involving introducing a hydrophobic side chain through an amide bond. In the manufacturing method, polyethylene glycol-co-polyaspartic acid benzyl ester or polyethylene glycol-co-polyglutamic acid benzyl ester is acetylated at the end in the same manner as described above. Then, a benzyl group is removed by alkali hydrolysis and the generated carboxyl group is subjected to a reaction with a hydrophobic side chain having an amino group. Alternatively, polyethylene glycol-co-polyaspartic acid benzyl ester or polyethylene glycol-co-polyglutamic acid benzyl ester and a compound having a primary amine are subjected to a reaction and then subjected to aminolysis to convert an ester bond to an amide bond. This allows the introduction of a hydrophobic side chain through an amide bond. In addition, a poly(amino acid derivative) segment including a hydrophobic side chain having a hydrophobic group whose end has been substituted by an amino group and a hydrophobic side chain without amino group substitution may also be obtained by adding a primary amine such as 1-octylamine to polyethylene glycol-co-polyaspartic acid benzyl ester in an organic solvent so as to achieve a desired amidation ratio, subjecting the mixture to a reaction for a predetermined period of time, and then adding a large excess amount of 1,8-diaminooctane or the like to an unconverted benzyl ester.
The block copolymer with HDL affinity has an HDL transfer rate, which is determined as described below, of 30% or more owing to its affinity with HDL. The block copolymer with HDL affinity has an HDL transfer rate of preferably 40% or more, more preferably 45% or more, particularly preferably 50% or more.
[Method of Determining HDL Transfer Rate]
Block copolymers are used as a polymer micelles encapsulating lysozyme, and the polymer micelles are incubated in plasma at 37° C. for 24 hours. After that, the respective lipoprotein fractions are purified and collected. The concentration of the block copolymers in each of the collected VLDL, LDL, HDL, and residual fractions is measured. Then, the content (on the weight basis) of the block copolymers in each of the fractions is calculated based on the volume and block copolymer concentration in each of the fractions. The resultant value is substituted for the following equation to determine an HDL transfer rate.
HDL transfer rate (%)=Block copolymer content in HDL fraction/Total of block copolymer contents in respective fractions×100
In determining the HDL transfer rate, the block copolymer with HDL affinity is preferably present in an HDL fraction in the highest amount among other lipoprotein fractions (excluding a chylomicron fraction). That is, it is preferred that the content of the block copolymer with HDL affinity in the HDL fraction be highest among the contents of the block copolymer with HDL affinity in the respective fractions, i.e., VLDL, LDL, HDL, and residual fractions.
The polymer micelle composition may further include a block copolymer without HDL affinity as one of the block copolymers each having a hydrophobic polymer chain segment and a hydrophilic polymer chain segment. It is difficult to detach the block copolymer without HDL affinity preferentially from the polymer micelle. This is because an entry into the interior of the polymer micelle is difficult for lipoproteins except HDL. Thus, when the polymer micelle composition is prepared as a mixed type of a block copolymer with HDL affinity and a block copolymer without HDL affinity, gap formation due to the detachment of the block copolymers with HDL affinity may be suppressed, and in some cases, gap formation may be promoted owing to a reduction in hydrophobic interaction between the block copolymers for forming the polymer micelle composition on the contrary. As described above, the release speed of a drug from the polymer micelle composition may be controlled by adjusting the contents of the block copolymer with HDL affinity and the block copolymer without HDL affinity. That is, according to the present invention, there can be provided a polymer micelle having disruptive property, which has been conventionally difficult to be imparted, and further, the control of the disintegration speed of the polymer micelle can also be facilitated.
The hydrophobic polymer chain segment in the block copolymer without HDL affinity may be formed of a polyamino acid including repeating units derived from a hydrophobic derivative of an amino acid obtained by introducing a hydrophobic group having a linear or branched structure into a side chain of the amino acid. The hydrophobic derivative of an amino acid is a hydrophobic derivative of preferably an acidic amino acid, more preferably aspartic acid and/or glutamic acid.
The hydrophobic group having a linear or branched structure is exemplified by a C4 to C18 unsubstituted or substituted linear or branched alkyl group, a C4 to C18 unsubstituted or substituted linear or branched alkenyl group, and a C4 to C18 unsubstituted or substituted linear or branched alkynyl group, preferably a C4 to C18 unsubstituted or substituted linear or branched alkyl group.
As for the hydrophilic polymer chain segment in the block copolymer without HDL affinity, the same hydrophilic polymer as in the case with the hydrophilic polymer chain segment in the block copolymer with HDL affinity may be selected. Further, the end modification of each of the hydrophilic polymer chain segment and the hydrophobic polymer chain segment in the block copolymer without HDL affinity and the linking of those segments are also as described in the paragraph relating to the block copolymer with HDL affinity.
The block copolymer without HDL affinity may be represented by each of the following general formulae (III) and (IV):
In each of the above-mentioned formulae, R9 and R11 each independently represent a hydrogen atom or a lower alkyl group substituted or unsubstituted by an optionally protected functional group;
p in each of the above-mentioned formulae represents an integer in the range of preferably 10 to 1,000, more preferably 20 to 600, particularly preferably 50 to 500. q and r in each of the above-mentioned formulae each represent an integer in the range of preferably 20 to 200, more preferably 30 to 100.
The optionally protected functional group is as described in the paragraph relating to each of the formulae (I) and (II).
The HDL transfer rate of the block copolymer without HDL affinity may be less than 30%, preferably 25% or less, more preferably 20% or less.
The content ratio of the block copolymer with HDL affinity to the block copolymer without HDL affinity in the polymer micelle composition of the present invention (block copolymer with HDL affinity:block copolymer without HDL affinity, weight ratio) may be set depending on the intended use of the polymer micelle composition, the HDL transfer rate of each of the block copolymers, and the like. The content ratio (block copolymer with HDL affinity:block copolymer without HDL affinity, weight ratio) may be, for example, in the range of 1:99 to 99:1, in the range of 3:97 to 97:3, in the range of 15:85 to 85:15, or in the range of 40:60 to 60:40. As described above, the weight ratio of the block copolymer with HDL affinity with respect to the total weight of the block copolymer with HDL affinity and the block copolymer without HDL affinity in the polymer micelle composition may be, for example, 60% or less, 50% or less, 40% or less, 20% or less, 10% or less, 5% or less, 2% or less, or 1% or less. There is a tendency that the disintegration of the polymer micelle is induced to promote the release of a drug when the content ratio of the block copolymer with HDL affinity is large. Meanwhile, there is a tendency that the disintegration of the polymer micelle and the attendant release of a drug are suppressed when the content ratio of the block copolymer with HDL affinity is small.
B. Pharmaceutical Composition
A pharmaceutical composition of the present invention includes the polymer micelle composition described in the above-mentioned section A and a drug encapsulated in the polymer micelle composition. The drug is desirably one kind selected from the group consisting of water-soluble physiologically active polypeptides and proteins. In addition, the drug has a molecular weight of desirably 1,500 or more, preferably 2,000 or more. Preferred examples of the physiologically active polypeptides and proteins include: interferons α, β, and γ; erythropoietin; G-CSF; growth hormone; interleukins; tumor necrosis factor; granulocyte-macrophage colony-stimulating factor; macrophage colony-stimulating factor; hepatocyte growth factor; TGF-β superfamily; EGF; FGF; IGF-I; and blood coagulation factors typified by Factor VII. Further, as long as the activities are not impaired, derivatives of the above-mentioned proteins, more specifically, proteins having substitutions, additions, or deletions in one or more amino acids may be used as medicaments.
The drug may be a poorly water-soluble drug having a water solubility of 100 μg/mL or less. Examples of the poorly water-soluble drug include: anti-cancer agents such as paclitaxel, topotecan, camptothecin, cisplatin, daunorubicin hydrochloride, methotrexate, mitomycin C, docetaxel, vincristine sulfate, and derivatives thereof; polyene-based antibiotics such as amphotericin B and nystatin; and lipophilic drugs such as prostaglandins and derivatives thereof. The poorly water-soluble drug has a relatively small size but may be difficult to be released from a conventional type polymer micelle composition owing to its high hydrophobicity. On the other hand, the pharmaceutical composition of the present invention is also excellent for use in promoting the release of such poorly water-soluble drug as compared to the conventional type polymer micelle composition.
The amount of the drug to be encapsulated may be set depending on the intended use of the pharmaceutical composition and the like. The amount of the drug to be used is generally 0.01 to 50 wt %, preferably 0.1 to 10 wt % with respect to the total of the block copolymers in the polymer micelle composition.
The particle diameter of the polymer micelle encapsulating a drug is not particularly limited as long as it is a size capable of being administered to a living body. The particle diameter is preferably 10 μm or less, more preferably 5 μm or less. In particular, when the polymer micelle is used in intravenous administration, the particle diameter is preferably 500 nm or less, more preferably 300 nm or less.
The pharmaceutical composition may be prepared as described below, for example. First, the above-mentioned block copolymers are dissolved in an organic solvent. As necessary, the organic solvent may be removed by subjecting the resultant solution to air drying, e.g., drying to form a film under a nitrogen gas stream atmosphere and further drying under reduced pressure as necessary. To the block copolymers thus treated was added and mixed a solution containing a drug to be encapsulated. Then, a polymer micelle is formed from the resultant mixed solution while the drug is encapsulated.
Examples of the organic solvent include: non-water-miscible organic solvents such as dichloromethane, chloroform, diethyl ether, dibutyl ether, ethyl acetate, and butyl acetate; water-miscible organic solvents such as methanol, ethanol, propyl alcohol, isopropyl alcohol, dimethylsulfoxide, dimethylformamide, dimethylacetamide, acetonitrile, acetone, and tetrahydrofuran; and mixed solvents thereof.
The polymer micelle encapsulating a drug may be formed, for example, by stirring a mixed solution of block copolymers and a drug while applying the solution with energy by ultrasonic irradiation. The ultrasonic irradiation may be performed, for example, using a biodisruptor (manufactured by NIHONSEIKI KAISHA LTD.).
C. Method of Controlling Release Speed of Drug from Pharmaceutical Composition
The method involves changing the content ratio of the block copolymer with HDL affinity with respect to the total of the block copolymers in the polymer micelle composition in the pharmaceutical composition described in the above-mentioned section B. The block copolymer with HDL affinity is capable of exerting an effect of promoting the release of a drug from a polymer micelle. Thus, the content ratio of the block copolymer with HDL affinity may be changed to control the release speed of a drug from a polymer micelle.
For example, the content ratio of the block copolymer with HDL affinity with respect to the total of the block copolymers in the polymer micelle composition (content of block copolymer with HDL affinity/total of contents of block copolymers, weight ratio) is set in the range of more than 0/100 to 100/100 or less, preferably 1/100 to 100/100. More specifically, the content ratio of the block copolymer with HDL affinity with respect to the block copolymer without HDL affinity in the polymer micelle composition (block copolymer with HDL affinity:block copolymer without HDL affinity, weight ratio) is set, for example, in the range of 1:99 to 99:1, in the range of 3:97 to 97:3, in the range of 15:85 to 85:15, or in the range of 40:60 to 60:40. There is a tendency that the release of a drug may be promoted when the content ratio of the block copolymer with HDL affinity is large, whereas the release of a drug may be suppressed when the content ratio is small.
In the following description, for the purpose of simplified expression, for example, when a block copolymer has a hydrophilic polymer chain segment formed of a PEG chain having an average molecular weight of 10,000 and a hydrophobic polymer chain segment formed of a polyamino acid chain having 40 amino acid residues on average, and has an introduction rate of a benzyl group into a side chain of the polyamino acid chain of about 65%, the expression “block copolymer (10-40, 65% Bn)” is used. Similarly, when hydrophobic groups to be introduced into a side chain of the polyamino acid chain are an octyl group and a cholesteryl group, the expressions “block copolymer (10-40, 65% C8)” and “block copolymer (10-40, 65% Chol)” are used, respectively. The introduction rate of a hydrophobic group of about 65% includes 62 to 68%.
The block copolymers described in the following general formula (V) and Table 1 were used as block copolymers. Each of the block copolymers was weighed in a vial and purified water was added thereto so as to achieve a polymer concentration of 5 mg/mL. Then, the polymer solutions were vigorously stirred at 4° C. overnight. The polymer solutions were subjected to ultrasonic irradiation (in an ice water bath, Low, interval of 1 second, 10 minutes) using a biodisruptor (High Power Unit manufactured by NIHONSEIKI KAISHA LTD.) and then treated with a 0.22-μm membrane filter. Thus, empty micelle solutions each having a polymer concentration of 5 mg/mL are obtained. To each of the empty micelle solutions (0.6 mL) were added al mg/mL lysozyme solution (0.15 mL) so as to achieve a concentration of 5% (w/w) with respect to the polymer, a 200 mM sodium phosphate buffer (pH 6), and purified water. The resultant mixtures were adjusted with 0.1 N HCl so as to finally achieve a polymer concentration of 3 mg/mL, a lysozyme concentration of 0.15 mg/mL, and a composition of a 20 mM sodium phosphate buffer as well as a pH of 6. The solutions were inverted and swirled two or three times and then left to stand still at 4° C. overnight. The micelles each encapsulating lysozyme prepared as described above were warmed to room temperature, and then they were used.
In the above-mentioned formula, a glutamic acid unit and its hydrophobic derivative unit are bound to each other in any suitable order and are present at random in one block copolymer.
The polymer micelles each encapsulating lysozyme prepared in Reference Example 1 were used to determine an HDL transfer rate of each of the block copolymers. A specific experimental method is described below. To 810 μL of rat plasma stored at −80° C. after the centrifugation of blood collected with heparin from each of 8-week-old male Wistar rats were added 90 μL each of the polymer micelles each encapsulating lysozyme, and the mixture was incubated at 37° C. for 24 hours (final lysozyme concentration: 15 μg/mL, final polymer concentration: 300 μg/mL). The mixture was then subjected to ultracentrifugation under the conditions of 45,000 rpm (about 100,000 g), 15 minutes, and 4° C. (Rotar: MLA-130, Centrifuge tube: thick-walled polyallomer tube) using an “OptimaMAX” (trade name) (manufactured by Beckman) in accordance with the protocol of Axis-Shield Density Gradient Media downloadable from http://www.axis-shield-density-gradient-media.com/CD2009/macro mol/M07.pdf. Then, a chylomicron fraction as the uppermost layer was removed from the plasma after ultracentrifugation. After that, 180 μL of an “Optiprep (registered trademark)” (trade name) (manufactured by Axis-shield) in a ¼ volume of the plasma were added and mixed with respect to 720 μL of the plasma, and the mixture was subjected to ultracentrifugation under the conditions of 85,000 rpm (about 350,000 g), 3 hours, and 16° C. During the ultracentrifugation, balance adjustment was carried out using a 0.85% (w/v) NaCl/10 mM 2-[4-(2-hydroxyethyl)-1-piperazinyl]-ethanesulfonic acid (HEPES) buffer (pH 7.4). After the ultracentrifugation, VLDL, LDL, HDL, and residual (other) fractions were collected and the block copolymer concentration in each of the fractions was measured using a PEG-ELISA kit (manufactured by Life Diagnostics). Based on the resultant polymer concentration and the volume of each of the fractions, the content of the block copolymer in each of the fractions and its ratio (i.e., transfer rate of block copolymer to each fraction) were calculated.
As seen from
PEG-pGlu (10-40, 30% Chol) was used as a block copolymer. The block copolymer was weighed in a vial. A 20 mM 2-morpholino ethanesulfonic acid monohydrate (MES) buffer (pH 5) was added thereto so as to achieve a polymer concentration of 2 mg/mL and the mixture was vigorously stirred at 4° C. overnight. The polymer solution was subjected to ultrasonic irradiation (in an ice water bath, Low, interval of 1 second, 10 minutes) using a biodisruptor (High Power Unit manufactured by NIHONSEIKI KAISHA LTD.) and then treated with a 0.22-μm membrane filter. Thus, an empty micelle solution having a polymer concentration of 2 mg/mL was obtained. To the resultant empty micelle solution (6 mL) was added a 300 μg/mL G-CSF solution (2 mL) so as to achieve a concentration of 5% (w/w) with respect to the polymer and the mixture was inverted and swirled and then left to stand still at 4° C. overnight. After that, the solution was purified and concentrated by ultrafiltration using an “Amicon Ultra (registered trademark)” (trade name) (manufactured by Millipore Corporation, cutoff molecular weight: 100,000), and the medium was replaced by a 10% (w/w) sucrose aqueous solution. The collected polymer micelle encapsulating G-CSF was stored at −80° C. and thawed at room temperature before use.
The solution of the polymer micelle encapsulating G-CSF obtained above was administered to male Wistar rats via the tail vein. The dosage was 100 μg/kg of body weight and the number of animals for the sample was three. Blood was collected with a heparin-treated syringe from the jugular vein under ether anesthesia 5 minutes, 1 hour, 6 hours, 1 day, 2 days, and 3 days after the administration. The plasma G-CSF concentration was measured using a G-CSF-ELISA kit (manufactured by RayBiotech, Inc.).
(2) PEG-pGlu (10-40, 60% C8)
A polymer micelle encapsulating G-CSF was prepared in the same manner as in the test example using PEG-pGlu (10-40, 30% Chol) except that PEG-pGlu (10-40, 60% C8) was used as the block copolymer and the number of animals for the sample was nine. The time-courses of plasma G-CSF concentration were examined.
(3) Mixed Polymer Micelle
PEG-pGlu (10-40, 30% Chol) and PEG-pGlu (10-40, 60% C8) were each weighed in an equal amount and both of the polymers were dissolved in dichloromethane and completely homogenized. After that, the solvent was removed using a shaking concentrator to produce a film. An empty micelle was then obtained in accordance with a conventional method. G-CSF was then encapsulated into the empty micelle so as to achieve a concentration of 5% (w/w) with respect to the polymers in accordance with a conventional method. The resultant polymer micelle encapsulating G-CSF was administered to rats to examine the time-courses of plasma G-CSF concentration.
(4) Direct Administration of G-CSF
The time-courses of plasma G-CSF concentration was examined in the same manner as in the test example using PEG-pGlu (10-40, 30% Chol) except that a G-CSF solution (100 μg/mL) was used in place of the solution of the polymer micelle encapsulating G-CSF and the number of animals for the sample was five.
As illustrated in
PEG-pGlu (10-40, 90% C8) was used as a block copolymer. The block copolymer was weighed in a vial. A 20 mM MES Buffer (pH 5) including 13.3% sucrose was added thereto so as to achieve a polymer concentration of 10 mg/mL, and the mixture was vigorously stirred at 4° C. overnight. The polymer solution was subjected to ultrasonic irradiation (in an ice water bath, High, interval of 1 second, 15 minutes×3) using a biodisruptor (NIHONSEIKI KAISHA LTD., High Power Unit) and then treated with a 0.22-μm membrane filter. To the solution was added the above-mentioned 20 mM MES Buffer (pH 5) including sucrose and the polymer concentration was adjusted to 2 mg/mL to obtain an empty micelle solution. To the resultant empty micelle solution (1.2 mL) was added a 300 μg/mL G-CSF solution (0.4 mL) so as to achieve a concentration of 5% (w/w) with respect to the polymer, and the mixture was inverted and swirled, left to stand still at 4° C. overnight, and then stored at −80° C. The stored mixture was thawed at room temperature before use.
(2) Bn-Type Micelle
A polymer micelle encapsulating G-CSF was prepared in the same manner as in the test example of the C8-type micelle except that PEG-pGlu (10-40, 100% Bn) was used as the block copolymer.
(3) Mixed-Type Micelle
PEG-pGlu (10-40, 90% C8) and PEG-pGlu (10-40, 100% Bn) were each weighed in a vial and completely dissolved with acetone so as to achieve a polymer concentration of 10 mg/mL. The solutions were mixed with each other so that the weight ratios of PEG-pGlu (10-40, 90% C8) to PEG-pGlu (10-40, 100% En) were 19:1, 4:1, and 1:1. After that, the solvent was removedusing a shaking concentrator to produce a film. Then, an empty micelle was obtained in accordance with a conventional method. Then, G-CSF was encapsulated into the empty micelle so as to achieve a concentration of 5% (w/w) with respect to the polymers in accordance with a conventional method.
Those solutions of the polymer micelles each encapsulating G-CSF were administered to male Wistar rats (6-week-old) via the tail vein under light ether anesthesia. The dosage was 100 μg/kg of body weight and the number of animals for the sample was three for each solution. Blood was collected with a heparin-treated syringe 24 hours after the administration, and EDTA-2Na was added so that the final concentration was 1 mg/ml. In this state, the number of neutrophils was measured using a multiple automated hematology analyzer for veterinary use (pocH-100iV Diff manufactured by SYSMEX CORPORATION). Based on the resultant measured values, drug release coefficients (%) of the Bn-type micelle and various mixed-type micelles were calculated in accordance with the following equation. Table 2 shows the calculated drug release coefficients of the polymer micelles. It is conceivable that the larger coefficient should mean that the polymer micelle has a stronger action of actively releasing a drug than the C8-type micelle.
Drug release coefficient (%)=100×(A−B)/(A−C)
As described above, also in the case where a benzyl type polymer was selected as the block copolymer with HDL affinity, the release speed of a drug can be controlled by employing a mixed-type micelle.
A polymer micelle encapsulating G-CSF was prepared in the same manner as in the test example of the C8-type micelle of Example 2.
A polymer micelle encapsulating G-CSF was prepared in the same manner as in the test example of PEG-pGlu (10-40, 30% Chol) except that PEG-pGlu (10-40, 25% Chol) was used as the block copolymer.
G-CSF was encapsulated in an empty micelle in the same manner as in Example 2 except that: PEG-pGlu (10-40, 25% Chol) was used in place of PEG-pGlu (10-40, 100% Bn); dichloromethane was used as the solvent for dissolving PEG-pGlu (10-40, 90% C8) ; and PEG-pGlu (10-40, 90% C8) and PEG-pGlu (10-40, 25% Chol) were mixed with each other at weight ratios of 19:1 and 4:1.
The number of neutrophils was measured in the same manner as in Example 2 except that the number of animals for the sample was six. Based on the resultant measured values, drug release coefficients (%) of the Chol-type micelle and various mixed-type micelles were calculated in the same manner as in Example 2. Table 3 shows the calculated drug release coefficients of the polymer micelles.
As described above, also in the case where a cholesterol type polymer was selected as the block copolymer with HDL affinity, the release speed of a drug can be controlled by employing a mixed-type micelle.
A polymer micelle encapsulating G-CSF was prepared in the same manner as in the test example of the C8-type micelle of Example 2.
A polymer micelle encapsulating G-CSF was prepared in the same manner as in the test example of the Chol-type micelle of Example 3.
(3) Mixed Polymer Micelle
Polymer micelles each encapsulating G-CSF were prepared by mixing PEG-pGlu (10-40, 90% C8) and PEG-pGlu (10-40, 25% Chol) at weight ratios of 19:1, 4:1, and 1:1 in the same manner as in the test example of the mixed polymer micelle of Example 3.
The solutions of the polymer micelles each encapsulating G-CSF obtained above were administered to male Wistar rats via the tail vein. The dosage was 100 μg/kg of body weight and the number of animals for the sample was three for each solution. Blood was collected with a heparin-treated syringe from the jugular vein under ether anesthesia 5 minutes, 1 hour, 6 hours, 1 day, 2 days, and 3 days after the administration, and the plasma G-CSF concentration was measured using a G-CSF-ELISA kit (manufactured by RayBiotech, Inc.).
| Number | Date | Country | Kind |
|---|---|---|---|
| 2010-024323 | Feb 2010 | JP | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/JP2011/052475 | 2/7/2011 | WO | 00 | 12/29/2011 |
